Cardiac Prosthesis

ABSTRACT

Systems, devices and methods for resizing a valve annulus are described. An implant is delivered proximate a mitral valve, the implant comprising a tubular body and a plurality of piercing helical anchors, the tubular body comprising an proximal diameter and a distal diameter. Tissue proximate the mitral valve is engaged by rotating the plurality of anchors with corresponding rotational drivers. The tubular body may be transitioned from a first structural configuration having the proximal diameter smaller than the distal diameter to a second structural configuration having the proximal diameter larger than the distal diameter.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation of Ser. No. 17/081,128, filed Oct. 27, 2020, which is a continuation of Ser. No. 15/423,374, filed Feb. 2, 2017, which claims the benefit of priority to U.S. Provisional Application No. 62/291,347, filed on Feb. 4, 2016, and which is a Continuation-in-Part Application of U.S. application Ser. No. 14/427,909, filed on Mar. 12, 2015, which is a U.S. National Phase Application of PCT International Application No. PCT/US2013/059751, filed on Sep. 13, 2013, designating the United States of America and published in the English language, which is an International Application of and claims the benefit of priority to U.S. Provisional Application No. 61/700,989, filed on Sep. 14, 2012. Each of the above-referenced applications are hereby expressly incorporated by reference herein in their entireties for all purposes and form a part of this specification. Any and all priority claims identified in the Application Data Sheet, or any correction thereto, are hereby incorporated by reference under 37 C.F.R. § 1.57.

BACKGROUND Field

This disclosure relates generally to cardiac treatment devices and techniques, and in particular, to methods and devices for repair of mitral valve defects such as mitral valve regurgitation.

Background of Related Art

The mitral valve is one of four heart valves that direct blood through the two sides of the heart. The mitral valve itself consists of two leaflets, an anterior leaflet and a posterior leaflet, each of which are passive in that the leaflets open and close in response to pressure placed on the leaflets by the pumping of the heart.

Among the problems that can develop or occur with respect to the mitral valve is mitral valve regurgitation (MR), in which the mitral valve leaflets become unable to close properly, thus causing leakage of the mitral valve. Severe mitral regurgitation is a serious problem that, if left untreated, can adversely affect cardiac function and thus compromise a patient's quality of life and life span.

Currently, mitral regurgitation is diagnosed by many indicators, and the mechanism of mitral regurgitation can be accurately visualized by trans-esophageal echocardiography or fluoroscopy with dye injection. The most prevalent and widely accepted current technique to correct mitral regurgitation is to repair the mitral valve via open-heart surgery while a patient's heart is stopped and the patient is on cardiopulmonary bypass, a highly invasive procedure that has inherent risks.

SUMMARY

In one aspect, a method is described comprising inserting an implant proximate a mitral valve, the implant comprising a tubular body and a plurality of piercing members, the tubular body comprising an upper (i.e. proximal) diameter and a lower (i.e. distal) diameter. The method also includes engaging tissue proximate the mitral valve by the plurality of piercing members and transitioning the tubular body from a first structural configuration to a second structural configuration by application of an expansive force to the tubular body proximate the upper diameter, the first structural configuration having the upper diameter smaller than the lower diameter and the second structural configuration having the upper diameter larger than the lower diameter.

In another aspect, an implant is described comprising a tubular body comprising an upper diameter and a lower diameter, the tubular body having a first structural configuration in which the upper diameter is smaller than the lower diameter and a second structural configuration in which the upper diameter is larger than the lower diameter, the tubular body configured to transition from the first structural configuration to the second structural configuration by application of an expansive force to the tubular body proximate the upper diameter. The implant also comprises a plurality of piercing members connected to the tubular body and proximate the lower diameter to engage tissue proximate a mitral valve.

In another aspect, a system is described comprising a guide wire, a sheath over the guide wire, and an implant for delivery to a body by traveling through the sheath and along the guide wire. The implant comprises a tubular body comprising an upper diameter and a lower diameter, the tubular body having a first structural configuration in which the upper diameter is smaller than the lower diameter and a second structural configuration in which the upper diameter is larger than the lower diameter, the tubular body configured to transition from the first structural configuration to the second structural configuration by application of an expansive force to the tubular body proximate the upper diameter. The implant also comprises a plurality of barbs connected to the tubular body and proximate the lower diameter to penetrate tissue proximate a mitral valve.

In another aspect, a delivery system for delivering an implant within the heart for reducing the size of a heart valve annulus is described. The delivery system comprises a plurality of rotatable drivers and the implant. The plurality of rotatable drivers is configured to extend through one or more lumens of the delivery system. The implant is configured for delivery within the heart by traveling through the one or more lumens of the delivery system. The implant comprises a tubular body and a plurality of helical anchors. The tubular body comprises a frame defining a proximal diameter and a distal diameter. The tubular body has a first structural configuration in which the proximal diameter is smaller than the distal diameter and a second structural configuration in which the proximal diameter is larger than the distal diameter. The plurality of helical anchors are connected to the tubular body proximate the distal diameter of the frame. The plurality of helical anchors are configured to be rotated by the rotatable driver to advance the plurality of helical anchors distally relative to the frame and penetrate the heart valve annulus. In some embodiments of the delivery system, the implant may further comprise a series of distal apices and a series of holes. The series of distal apices may be formed by the frame proximate the distal diameter. The series of holes may be in each of the distal apices and are sized and spaced to receive therethrough a corresponding helical anchor for rotational engagement of the distal apex by the corresponding helical anchor. The plurality of rotatable drivers and the implant may be configured for transcatheter delivery of the implant to the heart. The delivery system may further comprise a delivery catheter comprising the one or more lumens of the delivery system. A distal end of the delivery catheter may be configured to advance through an opening in the femoral vein, through the femoral vein and into the right atrium of the heart, and through the septum of the heart into the left atrium. The delivery system may further comprise a location ring configured to be located on a side of the heart valve opposite the implant and to couple with the implant. The location ring may be separate from the implant and configured to be located on a side of the heart valve opposite the implant to assist in positioning the implant. The location ring may be configured to be removed from the heart after the implant is positioned and the plurality of helical anchors penetrate the heart valve annulus. The delivery system may comprise one lumen configured to receive therethrough an intracardiac echo catheter for visualizing a position of the implant relative to the mitral valve annulus. The delivery system may further comprise the intracardiac echo catheter. The implant may further comprise an expandable tubular member coupled with a proximal end of the frame and configured to expand to increase the proximal diameter of the frame. The expandable tubular member may be integral with the frame.

In another aspect, an implant for reducing the size of a heart valve annulus is described. The implant comprises a tubular body and a plurality of helical anchors. The tubular body comprises a frame defining a proximal diameter and a distal diameter. The tubular body has a first structural configuration in which the proximal diameter is smaller than the distal diameter and a second structural configuration in which the proximal diameter is larger than the distal diameter. The plurality of helical anchors are connected to the tubular body proximate the distal diameter of the frame. Each of the plurality of helical anchors is configured to be rotated by a plurality of rotatable drivers through a series of holes in lower apices of the frame to advance the plurality of helical anchors distally relative to the frame and penetrate the heart valve annulus.

In some embodiments, the implant further comprises an expandable tubular member proximate a proximal end of the frame, wherein when force is applied to the expandable member, the expandable member expands and engages the proximal end of the frame causing the frame to invert from the first structural configuration to the second structural configuration. The expandable tubular member may be integral with the proximal end of the frame. The expandable tubular member may be a stent-like member positioned internally of the frame proximate the proximal diameter of the frame. The implant may be configured to be contracted to a delivery configuration for transcatheter delivery of the implant to the heart by a delivery system. The implant may further comprise an expandable tubular member coupled with a proximal end of the frame, wherein contracting the expandable tubular member for transcatheter delivery causes the proximal diameter of the frame to decrease relative to an unconstrained state, which causes the distal diameter of the frame to increase relative to the unconstrained state such that the proximal and distal diameters of the frame are approximately the same when delivered. The implant may further comprise angled segments of the frame forming distal apices of the frame proximate the distal diameter, and the series of holes in each of the distal apices may be sized and spaced to receive therethrough a corresponding helical anchor for rotational engagement of the distal apex by the corresponding helical anchor. The tubular body may be configured to transition from the first structural configuration to the second structural configuration by application of an expansive force to the tubular body proximate the proximal diameter.

BRIEF DESCRIPTION OF THE DRAWINGS

For a more complete understanding of the present disclosure and its features and advantages, reference is now made to the following description, taken in conjunction with the accompanying drawings, in which:

FIGS. 1A-1F illustrate an example embodiment of an implant in accordance with the present disclosure;

FIGS. 2A-2D illustrate an alternative example embodiment of an implant in accordance with the present disclosure;

FIGS. 3A-3B illustrate a further alternative example embodiment of an implant in accordance with the present disclosure;

FIGS. 4A-4B illustrate an additional example embodiment of an implant in accordance with the present disclosure;

FIG. 5 illustrates examples of delivery routes of an implant, in accordance with the present disclosure;

FIG. 6 illustrates an example embodiment of the present disclosure utilizing vibrations, in accordance with the present disclosure;

FIG. 7 illustrates an alternative example embodiment of the present disclosure utilizing vibrations, in accordance with the present disclosure; and

FIG. 8 illustrates an additional example embodiment of the present disclosure utilizing vibrations, in accordance with the present disclosure.

FIGS. 9A-9B are perspective views of other embodiments of implants having rotatable helical anchors for securing the implants to a valve annulus.

FIG. 10-12 are perspective views of another embodiment of an implant, having an expandable tubular element, and configured to be secured to a valve annulus with helical anchors.

FIG. 13 is a perspective view of an embodiment of a delivery system shown delivering an embodiment of the implant of FIGS. 10-12 .

FIG. 14 is a perspective view of an embodiment of a delivery system shown delivering the implant of FIG. 9A.

FIGS. 15A-15D are sequential views of an embodiment of a transcatheter delivery system for delivering the implant of FIG. 9A showing an embodiment of a method for the delivery, positioning and anchoring of the implant.

DETAILED DESCRIPTION

The present disclosure relates to an implant including a tubular body and piercing members for reshaping a mitral valve suffering from mitral regurgitation. The implant may include two or more structural configurations. In a first structural configuration, an upper, i.e. proximal, diameter (away from the mitral valve) may be smaller than a lower, i.e. distal, diameter (proximate the mitral valve). In this first structural configuration, the piercing members of the implant may engage the tissue proximate the mitral valve, for example, the mitral valve annulus. The implant may then be transitioned from the first structural configuration to a second structural configuration in which the size of the upper diameter is larger than the lower diameter. This may be facilitated by an expansive force causing the upper diameter to expand, in turn causing the lower diameter to contract. As the lower diameter contracts, the penetrating members engaged with the tissue proximate the mitral valve may cause the mitral valve to also contract to a smaller diameter. This may allow the valve leaflets to close properly, addressing mitral regurgitation. FIGS. 1A-F illustrate one embodiment of an implant. For example, as shown in FIG. 1A, in some embodiments, repair of a mitral valve may be achieved by a catheter system and catheterization procedure, wherein a catheter may be configured for percutaneous access to the mitral valve through the left ventricle. Access may be granted to the left ventricle through the apex of the heart where an incision may be made to insert a dilator and sheath 150 for access of a repair catheter 140. Sheath 150 may measure about six French to about thirty French and a closure device may be used in conjunction with the entry of this access catheter 140.

In one embodiment of the present disclosure, catheter 140 may include an extendable guide wire assembly 160, which may guide the system into position. Guide wire 160 may measure between 0.010 inches and 0.038 inches in diameter, and may be 0.035 inches in diameter. Catheter 140 or sheath 150 when accessed through the apex of the heart may measure about twenty to thirty centimeters in length.

As shown in FIG. 1B, once access has been achieved, a delivery system may be introduced through sheath 150 along guide wire 160 with implant 110 for reducing the diameter of the mitral valve annulus. Catheter 140 may deliver implant 110 to resize the mitral valve to reduce the mitral valve cross sectional area or move the posterior leaflet back into position limiting or reducing mitral valve regurgitation.

Implant 110 may include a tubular body with portions of the tube removed similar to a stent structure where a portion of the material may be removed via laser cutting or other means to selectively cut portions of the tube away forming a radially-expandable tubular body.

Implant 110 may be introduced in a collapsed structural configuration. This collapsed structural configuration may allow implant 110 to fit within sheath 150 to allow for a percutaneous procedure rather than an open-heart procedure. As shown in FIG. 1B, once implant 110 arrives in the left atrium, implant 110 may be expanded to a larger first structural configuration to engage tissue proximate the mitral valve, for example, the mitral valve annulus. In one embodiment, implant 110 may have a tubular shape with a free diameter of about twenty five to about thirty five millimeters in diameter, a height of about ten to about thirty millimeters, and a wall thickness of between about 0.005 inches and about 0.040 inches. Implant 110 may be constructed of a metallic material such as stainless steel, MP35N alloy, Nitinol or other implantable material.

In some embodiments, implant 110 may be tapered such that one end may be larger in diameter than the other end, appearing generally frustoconical in shape. The diameters of the ends may be approximately twenty five millimeters on the smaller end and approximately thirty five millimeters on the larger end. Implant 110 may also be non-circular where a portion of the implant may be elliptical or include a radial portion that is flat. This flat portion may be oriented toward the aortic valve and the circular portion may be positioned toward the posterior leaflet. To facilitate discussion of implant 110, an upper portion and lower portion may be described. The lower portion may refer to the end of implant 110 proximate mitral valve 170 while the upper portion may refer to the end of implant 110 free in the left atrium.

Implant 110 may include piercing members 115 proximate the lower portion of implant 110 proximate mitral valve 170 to engage with tissue proximate mitral valve 170, for example, the mitral valve annulus. Piercing members 115 may include barbs or hooks similar to fish hook barbs or other similar feature to resist withdrawal from tissue once pierced. Piercing members 115, barbs or hooks of the piercing members 115, or any combination thereof may pierce the tissue to engage with the tissue. Piercing members 115 may include a singular barb or hook, or a plurality of barbs or hooks per piercing member 115. Piercing members 115 may be immediately exposed or covered for delivery. They may number from one to fifty and may have a length of about four to twenty millimeters in length. They may have the same wall thickness as a wall of the tubular body of implant 110 or may differ with an increased or decreased thickness or taper in either direction to allow for mechanical integrity.

Piercing members 115 of implant 110 may be integral or attached to implant 110 as a secondary component glued, welded, or attached as an ancillary part. Piercing members 115 may also be laser cut into implant 110, and therefore attached to implant 110. The barbs or hooks may be fatigue resistant from fracture or separation from piercing members 115. For example, the barbs or hooks may have additional strength or wall thickness at the connection to piercing members 115. The barbs or hooks may also be attached with a hinged attachment allowing motion relative to the heart, but not longitudinally where the barbs or hooks may separate from piercing member 115.

The barbs or hooks of piercing member 115 may be active or passive meaning that the barbs or hooks may be activated with heat to bend or expose or mechanically formed through an external force to bend or expose. For example, each barb or hook may be sheathed inside a tube and removal of this tube may allow the barb or hook to be activated by, for example, body heat or some other activation factor, such that the barb or hook is exposed so as to engage the surrounding tissue. In a passive configuration, the barbs or hooks may be static in nature and either always exposed or exposed as soon as a covering is removed. The barbs or hooks may be hidden until deployment limiting the exposure during delivery and positioning and only exposed once positioning is finalized. The exposure may be completed as individual barbs or as multiples of barbs. In some embodiments, the covering is thus only a temporary covering.

As shown in FIG. 1B, in some embodiments, implant 110 may be positioned at the annulus of mitral valve 170 where the mitral valve hinge meets the left ventricle and the left atrium meets mitral valve 170. Positioning implant 110 at this location may be facilitated using a location ring 120. For example, location ring 120 may be positioned within the left ventricle, under mitral valve 170. A catheter to deliver location ring 120 may be placed in the left ventricle via the same access point through sheath 150. In some embodiments, a catheter 130 may extend through the aorta to deliver and/or remove the location ring 120. The catheter 130 as shown may extend through the aorta and through the aortic valve, and enter the left ventricle. In some embodiments, the location ring 120 may be delivered and/or removed from the apical entry point, as mentioned, or from trans-aortic entry via a femoral entry. In some embodiments, location ring 120 may comprise a metallic ring or coiled section, which may be viewed via fluoroscopy or echo guidance to confirm the location of location ring 120. This may allow confirmation of a positive location for implant 110 to be located with respect to the mitral valve annulus. In addition to the use of a location ring, other methods for determining a desired location to attach implant 110 may could include echo guidance, CT, fluoroscopy or MRI other imaging techniques to highlight the mitral valve hinge.

As shown in FIG. 1C, while in a first expanded structural configuration, and once a proper position has been achieved, implant 110 may have a downward force “A” applied to cause piercing members 115 to engage with and/or pierce the mitral valve annulus. This force may be applied by the delivery system itself, or may be applied by a secondary catheter that may be introduced for engaging piercing members 115 with the tissue proximate mitral valve 170.

As shown in FIG. 1D, the location ring 120 may be used to locate the relative position of the implant 110 after anchoring the implant 110 to the annulus. For example, the location ring 120 may comprise a metallic ring or coiled section, which may be viewed via fluoroscopy or echo guidance to confirm the location of location ring 120 and implant 110. After confirmation of acceptable placement of the implant 110, or after inversion of the implant 110 as described below, the location ring 120 may then be removed. Thus, the location ring 120 may be temporary. The location ring 120 may thus be separate from the implant 110 and configured to be located on a side of the heart valve opposite the implant 110 to assist in positioning the implant 110. The location ring 120 may be configured to be removed from the heart after the implant 110 is positioned and the plurality of helical anchors penetrate the heart valve annulus. The location ring 120 may be removed by the same delivery system by which it was inserted, for example the delivery system shown in FIGS. 1A-1F, the catheter 130, etc.

In some embodiments, location ring 120 may also act as an anchor for implant 110. In such an embodiment, implant 110 above mitral valve 170 (i.e. in the left atrium side of mitral valve 170) may attach to location ring 120 below mitral valve 170 (i.e. in the left ventricle side of mitral valve 170). For example, the hooks or barbs of piercing members 115 may engage with location ring 120. This may be accomplished by a through suture, a barbed means, wrapping or clipping location ring 120 to implant 110. Magnetic forces may also hold location ring 120 and implant 110 together either temporarily or permanently. Alternatively, the hooks or barbs may also be attached to some other separate implant below mitral valve 170 in the left ventricle. This may be a wire, ring, or tee anchor to secure implant 110 to via wires, threads or mechanical means to attach through the tissue median. For convenience, this implant below mitral valve 170 may be referred to as location ring 120, even if not used in locating implant 110 proximate mitral valve 170.

In some embodiments, the shape of location ring 120 may be a circular cross section measuring about 0.010 inches to about 0.090 inches in diameter and may encircle the mitral annulus. The shape may also be non-circular, oval, biased to one axis or multi-axis to accommodate the multi-plane shape of mitral valve 170, which is more saddle shaped. It may also have a variable stiffness in different sections to accommodate tighter bends in the placement of location ring 120. Location ring 120 and or a delivery catheter may also be steerable to navigate the area under mitral valve 170 for ease of placement. Utilizing push pull wires to compress or load portions of the catheter or location ring 120 to predictably bend and orient the catheter or location ring 120 may allow a user to access difficult anatomical features en route to and around mitral valve 170.

As shown in FIG. 1E, once piercing members 115 have engaged the tissue proximate mitral valve 170, for example, the mitral valve annulus, an expansive force “B” may be applied to the upper portion of implant 110. By applying expansive force “B” to implant 110, a reactive reducing force “C” may also be produced at the lower portion of implant 110. As the diameter of the lower portion is decreased from reactive reducing force “C,” the diameter of mitral valve 170 is also reduced due to the attachment of implant 110 to the tissue around mitral valve 170. For example, once a sufficient reducing force “C” has been generated to reshape mitral valve 170 to a desired size, implant 110 may be left in a final position in which the size change of mitral valve 170 may be maintained. This may be a second structural configuration.

As shown in FIG. 1F, in some embodiments, piercing members 115 may engage the tissue proximate mitral valve 170 but not engage location ring 120. In such an embodiment, the barbs or hooks of piercing members 115 may bind, engage with, and/or resist withdrawal from tissue proximate mitral valve 170 in a manner sufficient to keep implant 110 attached to the tissue proximate mitral valve 170. Additionally, the binding, engaging, and/or resisting withdrawal may be sufficient to decrease the surface area of mitral valve 170 as expansive force “B” and reactive reducing force “C” are applied. In such an embodiment, location ring 120 may or may not be used to facilitate placing implant 110 at a positive location proximate mitral valve 170. In some embodiments, as described, the location ring 120 may not couple with the implant 110 but may be used to facilitate positioning of the implant 110, such as by temporarily positioning the location ring 120, etc. A positive location for implant 110 may be one in which implant 110 is able to engage tissue proximate mitral valve 170 without impairing the function of mitral valve 170 and further implant 110 may be used to decrease the surface area of mitral valve 170 as expansive force “B” and reactive reducing force “C” are applied.

FIGS. 2A-2D illustrate an example of implant 110 in accordance with the present disclosure. As shown in FIG. 2A, implant 110 may be made of a metal and cut to form a mesh, a cage, or series of repeating units to allow variations in diameter. For example, implant 110 may include a tubular body of repeating squares, diamonds, hexagons, or any other shape allowing a variation in diameter of implant 110. In first structural configuration as shown in FIG. 2A, implant 110 may have the larger diameter portion initially oriented toward mitral valve 170 (the lower portion with lower diameter 220) and the smaller diameter may be oriented in the left atrium (the upper portion with upper diameter 210). The upper portion may be in free space in the left atrium and have a smaller diameter ready to be expanded in this first structural configuration.

The construction of implant 110 may include a tapered laser cut tube expanded to a predetermined diameter with wall thickness approximately 0.005 inches to approximately 0.050 inches and a strut thickness of approximately 0.010 inches to approximately 0.070 inches and an expanded diameter of approximately 1.00 inch. If the implant is tapered, the large diameter may measure about thirty five millimeters in diameter and the smaller diameter may measure about twenty five millimeters in diameter. In the first structural configuration, the lower portion (i.e. the larger diameter section) may have penetrating members 115 to engage the mitral annulus and hold implant 110 in position during annuls reduction and remain as a permanent implant.

As shown in FIG. 2B, downward force “A” may be applied to implant 110. In some embodiments, piercing members 115A-H may be driven to engage the tissue one at a time. For example, a linear force may drive the hooks or barbs of piercing member 115A into the tissue by pushing at the top of implant 110 above piercing member 115A, thus transmitting a force through to the piercing member 115A, driving it into the tissue. The delivery system or catheter applying the force may then be rotated and actuated again to engage another piercing member 115, for example adjacent piercing member 115B. Once piercing member 115B has been engaged with the tissue, this may be repeated until all piercing members 115 have been engaged with the tissue. Alternatively, in some embodiments, force “A” may be sufficient to engage multiple piercing members 115 at once, rather than engaging only a single piercing member 115 at a time. In some embodiments, all of piercing members 115 may be engaged at once.

As shown in FIG. 2C, implant 110 may be in a first structural configuration in which upper diameter 210 may be smaller than lower diameter 220. An expansive force “B” may be applied to the upper portion of implant 110. As the expansive force “B” is applied such that the upper diameter 210 is increased, the lower diameter 220 may be decreased due to a reactive reductive force “C” which is generated. A wall of the tubular body of implant 110 may act as a beam in deflection where the upper portion of implant 110, when deflected (e.g. expanded), may cause the lower portion of implant 110 to bend (e.g. contract). This may facilitate the transition from this first structural configuration to a second structural configuration. The lower diameter 220 may be proximate piercing members 115, which are engaged with the mitral valve annulus. Thus, as lower diameter 220 becomes smaller, the diameter of mitral valve 170 becomes smaller. The expansive force “B” may be applied via balloon dilation, mechanical expansion or other means to increase upper diameter 210, thus reducing lower diameter 220. This may effectively invert implant 110's dimensions about axis 200, which may be referred to as an axis of inversion or axis of reflection. In some embodiments, the diameter of implant 110 at axis 200 may remain approximately uniform in a first structural configuration, transitioning between structural configurations, and a second structural configuration. As shown in FIG. 2D, the application of expansive force “B” and thus reactive reducing force “C” may result in implant 110 with upper diameter 210 having a larger length and lower diameter 220 having a shorter length. This may in turn reduce barb-engaged mitral valve 170 to a smaller annulus cross-sectional area, lessening the mitral regurgitation. The structural configuration shown in FIG. 2B may be the second structural configuration of implant 110 in which mitral valve 170 has been reduced in annulus cross-sectional area. Additionally, this second structural configuration may be a final structural configuration that may maintain the size change of mitral valve 170.

As shown in FIGS. 3A and 3B, an alternative method for applying an expansive force to implant 310 may be the deployment of a ring 320 within implant 310. FIG. 3A illustrates implant 310 in a first structural configuration and FIG. 3B illustrates implant 310 in a second structural configuration. The ring 320 may be formed of a shape memory material, such as nitinol. The ring 320 may be collapsed into a delivery catheter for delivery therethrough to the heart and ejected into or around the implant 310. In some embodiment, one or more releasable tethers may be attached to the ring 320. The releasable tethers may be pulled on to move the ring 320 and to release the tethers from the ring 320 after the ring 320 is in the desired location.

In some embodiments, a fixed ring 320 may be utilized. Fixed ring 320 may be moved vertically to expand the upper portion to increase upper, i.e. proximal, diameter 330, thus causing the lower portion to reduce lower, i.e. distal, diameter 340 along with the engaged tissue and mitral valve. For example, upward force “D” may be applied to ring 320. However, because of the frustoconical shape of implant 310, the upward force “D” may be translated to an expansive lateral force causing an increase in upper diameter 330. Ring 320 may lock into implant 310 by an interference fit or a mechanical stop built in ring 320 or implant 310, and may maintain implant 310 in the second structural configuration. In some embodiments, the fixed ring 320 may have a smaller diameter and initially be located at or near the upper diameter 330, thus restraining the upper diameter 330 and causing and/or maintaining the first structural configuration of the implant 310 shown in FIG. 3A. The fixed ring 320 may then be moved vertically downward as oriented toward the lower diameter 340, thereby allowing the upper diameter 330 to expand and increase in size and causing the lower diameter 340 to contract and reduce in size. The fixed ring 320 may then be located at or near the lower diameter 340 to cause and/or maintain the second structural configuration of the implant 310 shown in FIG. 3B.

Alternatively, an expandable ring 320 may be used rather than a fixed ring. Expandable ring 320 may be positioned within implant 310 and may be delivered and expanded by a catheter, for example using hydraulic or mechanical force to expand ring 320. Ring 320 may be introduced into implant 310's inner diameter where ring 320 may be tilted to allow for manipulation or positioning. Alternatively, ring 320 may be placed at a defined vertical position in implant 310 and ring 320 may be expanded, for example with mechanical or hydraulic force or an extension of the radial dimension. Ring 320 may also serve as a locking mechanism for implant 310 once the second structural configuration or the final position has been reached. The expansion and/or locking of ring 320 may be reversible in nature, thus undoing the expansion of the upper portion. Ring 320 may lock into implant 310, for example by an interference fit or a mechanical stop built in ring 320 and/or implant 310.

FIGS. 4A and 4B illustrate an additional embodiment of an implant 410 for reshaping mitral valve 170. FIG. 4A illustrates implant 410 in a first structural configuration and FIG. 4B illustrates implant 410 in a second structural configuration. As shown in FIG. 4A, in some embodiments, implant 410 may include one or more support beams 420 (for example, support beams 420A and 420B). Support beams 420 may facilitate the transition of expansive force “B” to the reductive force “C.” For example, support beam 420 may operate as a beam in deflection about axis 450. Thus, as expansive force “B” is applied to the upper portion of implant 410, beams 420A and 420B may act as levers with axis 450 as the fulcrum or point of rotation, causing reductive force “C” to reduce lower diameter 440. As expansive force “B” is applied to increase upper diameter 430 and decrease lower diameter 440, implant 410 may transition from a first structural configuration shown in FIG. 4A to a second structural configuration shown in FIG. 4B. As described above, this may reduce the cross-sectional area of mitral valve 170.

Support beams 420A and 420B may be integrally formed with implant 410, for example, as a thicker portion of a wall of the tubular body of implant 410, or a specific alignment of repeating units or elements of the structure of the wall of the tubular body. Alternatively, support beams 420A and 420B may be an additional support component added to implant 410. For example, they may be glued, welded, or otherwise permanently affixed to implant 410.

As shown in FIG. 5 , in addition to access to mitral valve 170 through the apex of the heart as shown by 510, access to mitral valve 170 may also be gained via the femoral artery as shown by 530, or via the femoral artery and through the aortic valve (for example, as described above with respect to delivery/removal of the location ring 120 through the aortic valve) or through the venous system and then via trans-septal puncture directly into the left atrium as shown by 520. When accessed via the femoral artery or trans-septally, a delivery catheter may measure about ninety to one hundred and fifty centimeters in length. The end of the catheter may be deflectable via deflection wires creating tension of bias to allow adjustments due to anatomical variations.

As shown in FIG. 6 , vibration may be applied directly to penetrating members 115 to facilitate the barbs or hooks and/or penetrating members 115 penetrating the tissue. Low frequency vibration, ultrasonic, or Radio Frequency energy may allow a lower insertion force compared to the barb or hook's and/or penetrating members' normal penetration force. Coupling this energy source to implant 110 may allow transmission of small vibrations 620 to the tip of each barb or hook and/or penetrating member 115. Alternatively, each barb or hook and/or penetrating member 115 may have its own independent energy source allowing a variable pattern of frequency or energy around implant 110. Direct tissue contact of the energy element or a coupling to implant 110 may be used but there may be a decrease in efficiency by coupling vibration 620 thereto. The frequency of vibration 620 may be about ten to one hundred Hz (cycles per second) or may be about twenty Hz.

As shown in FIGS. 7 and 8 , to aid in the engagement of the penetrating members 115, additional energy may be added to vibrate the tissue surrounding or below mitral valve 170. For example, as shown in FIG. 7 , vibration pads 710A and 710B may deliver vibration 620 to the surrounding tissue near the barbs or hooks of penetrating members 115. Pads 710A and 710B may be used to vibrate the tissue near the barb insertion site. Pads 710A and 710B may be completely separate from implant 110 or may be connected to the same delivery system. A separate control for linear and radial motion of pads 710A and 710B may be provided to control the location to provide precise delivery of vibration 620.

As shown in FIG. 8 , vibration pads 810A and 810B may also be located below mitral valve 170. This may still provide vibration 620 to facilitate the engagement of barbs or hooks of penetrating members 115 with tissue proximate mitral valve 170. As with the embodiment of FIG. 7 , vibration pads 810A and 810B may be completely separate from implant 110 or may be connected to the same delivery system. A separate control for linear and radial motion of pads 810A and 810B may be provided to control the location to provide precise delivery of vibration 620.

Radio frequency (RF) is a rate of oscillation in the range of about three kHz to three hundred GHz, which corresponds to the frequency of radio waves, and the alternating currents, which carry radio signals. RF usually refers to electrical rather than mechanical oscillations. Below is a chart of common nomenclature for different frequency ranges. The range utilized for barb penetration may be somewhere between ELF and HF as the goal is small vibration and not heating of the tissue. Possible user range selection would allow for different tissue types and densities.

TABLE 1 Frequency Wavelength Designation Abbreviation 3-30 Hz 10⁵-10⁴ km Extremely low ELF frequency 30-300 Hz 10⁴-10³ km Super low SLF frequency 300-3000 Hz 10³-100 km Ultra low ULF frequency 3-30 kHz 100-10 km Very low VLF frequency 30-300 kHz 10-1 km Low frequency LF 300 kHz-3 MHz   1 km-100 m  Medium MF frequency 3-30 MHz 100-10 m High frequency HF 30-300 MHz 10-1 m Very high VHF frequency 300 MHz-3 GHz     1 m-10 cm Ultra high UHF frequency 3-30 GHz 10-1 cm Super high SHF frequency 30-300 GHz 1 cm-1 mm  Extremely high EHF frequency 300 GHz-3000 GHz 1 mm-0.1 mm Tremendously THF high frequency

Vibration to enhance tissue penetration by the anchor may be delivered from a vibration source to tissue adjacent the penetration site, such as by the vibration pads discussed above. The vibration source may be embedded in the pad or other vibration interface at the distal end of an elongate control element such as a wire or tube. Alternatively, the vibration source may be located in a proximal manifold and propagate vibrational energy distally through an elongate wire or tube extending through the catheter body. The vibration source can alternatively be coupled in vibration propagating communication with either the implant frame or with each individual anchor directly, such as through the anchor driver, depending upon desired performance.

FIG. 9A depicts another embodiment of an implant 910. The implant 910 may have the same or similar features and/or functionalities as other implants described herein, and vice versa, except as otherwise described. Implant 910 comprises a frame 920, piercing members or anchors 930, and may include an expandable member 940. The frame 920 has a free or unconstrained state or, otherwise stated, nominal configuration as shown in FIG. 9A. The frame 920 may be made of a nickel titanium alloy, i.e. nitinol, or other shape memory alloy or metal. The frame 920 may be a dissimilar material as that of the expandable member 940. The frame 920 may be tubular with a wall circumferentially defining a central axis. The frame 920 may include angled segments as shown, and/or other segments, configurations, etc. The frame 920 as shown may be sinusoidally shaped, although its architecture could be of a diamond lattice or hexagonal lattice, for example. The frame 920 or portions thereof may incline radially outward with respect to the axis and/or with respect to the expandable member 940. The frame 920 may pivot about pivot joints located at or near interfaces with the expandable member 940. In some embodiments, fixed attachments are located at one or more of the joints between the frame 920 and the expandable member 940, for example at the interfaces of abutting apices of the frame 920 and the expandable member 940.

Anchors 930 may be metallic helical members. The anchors 930 may threadingly engage with the lower, i.e. distal, apices of frame 920. The anchors 930 may wind through a series of holes through holes drilled in the distal ends or distal apices of frame 920 (more clearly indicated by reference numerals 1050 in FIGS. 10, 11 and 12 ). The frame 920 may include a series of distal apices formed by the frame 920 proximate the distal diameter. A series of holes in each of the distal apices may be sized and spaced to receive therethrough a corresponding helical anchor 930 for rotational engagement of the distal apex by the corresponding helical anchor 930. The holes may be the same or similar to holes 1050 described for example with respect to FIG. 10 . The anchors 930 may be advanced distally, and in some embodiments retracted proximally, in a rotational or corkscrew type manner. The anchors 930 may extend distally relative to the frame 920. For example, as the anchors 930 are rotated, the anchors 930 may move in the distal direction while the frame 920 is stationary. In some embodiments, the frame 920 may move distally while the anchors 930 move farther distally relative to the frame 920. Thus, the frame 920 may be located in the preferred position and the anchors 930 may then be moved distally to secure into heart tissue while the frame 920 remains axially stationary or approximately axially stationary. This allows for better accuracy with positioning of the implant 910 because there is less movement of the frame 920 while the anchors 930 are being secured to heart tissue. Further, the anchors 930 engage the frame 920, as described, for example through the series of holes in distal apices of the frame 920. This allows for a secure attachment between the anchors 930 and the frame 920 without the need for additional structure or features. The arrangement of the holes and the corresponding receiving of the anchor 930 therethrough in each apex allows for an axially secure engagement of the anchor 930 and the frame 920 while still allowing for movement of the anchor 930 by driving it with the driver 952. By axially secure it is meant that the anchor 930 will not move axially relative to the frame 920 in the absence of sufficient rotational force acting on the anchor 930, such that the anchor 930 and frame 920 are rotationally secured together after removal of the rotational force from the driver 952 thereby impeding further axial movement of the anchor 930 relative to the frame 920. The configuration of the series of holes in the frame 920 and the helical shape of the anchors 930 allows for such advantages. In FIG. 9A, the anchors 930 are shown extended distally, for example in the final stage of deployment into cardiac tissue proximate the mitral annulus. The mitral annulus is that region of transition from the left atrium to the left ventricle and proximate and above the area where the leaflets of mitral valve 170 (see FIG. 5 ) hinge from the left ventricle.

The implant 910 may include the expandable portion or member 940. The expandable member 940 may be stent-like. The expandable member 940 may be tubular with a wall circumferentially defining a central axis. The expandable member 940 may include angled segments as shown, and/or other segments, configurations, etc. While shown in the shape of a sinusoid, the expandable member 940 may otherwise have a diamond lattice or hexagonal lattice architecture, for example. The expandable member 940 may be a dissimilar material as that of the frame 920. The expandable member 940 may be made of metallic alloys such as stainless steel, cobalt chromium, platinum iridium and the like. The expandable member 940 may be collapsed or crimped for insertion into a delivery system and forcibly expanded, so as to undergo plastic deformation, to invert the frame 920. As shown in FIG. 9A, expandable member 940 may be integral with frame 920, for example a unified, monolithic portion or region of the frame 920. In some embodiments, the expandable member 940 is fixedly attached to frame 920 by bonding, welding, sutures, metallic bands crimped on to each structure, or otherwise connected in a fixed relationship to frame 920. In some embodiments, the expandable member 940 can have other coupling interactions with the frame 920, such as a friction fit, expansive force keeping the frame 920 secured with the expandable member 940, etc.

Implant 910 is loaded into the distal end of a delivery system (not shown), by compressing or collapsing the frame 920. Anchors 930 would be initially retracted for loading and delivery. Once positioned in a desired location proximate the mitral valve annulus, frame 920 is advanced out of the delivery system and its distal apices are abutted to the target heart tissue for anchor placement. The helical anchors are then advance, by rotation thereof, into the target cardiac tissue thereby anchoring implant 910 into the region of the mitral valve annulus. Implant 910 is then fully released from the delivery system.

After implant 910 is fully released from the delivery system, expandable member 940 is then forcibly expanded, such as by a dilatation balloon, causing frame 920 to invert. Inversion of frame 920 causes the anchor bearing distal end of frame 920 to taper or contract, causing the mitral valve annulus to reduce in size thus limiting the mitral valve regurgitation.

FIG. 9B is another embodiment of an implant 912. The implant 912 may have the same or similar features and/or functionalities as the implant 910, and vice versa, except as otherwise noted. The implant 912 comprises the expandable member 940 and piercing members or anchors 930. A frame 922 extends circumferentially about a central longitudinal axis. The frame 922 is formed to have as its free or unconstrained configuration somewhat opposite to that of the frame 920 of the implant 910. For example, as shown the lower, distal end as oriented, the end engaging anchors 930, may be smaller in diameter than the opposite upper, proximal end of the frame 922. The frame 922 may therefore incline radially inward relative to the central axis and/or relative to the expandable member 940. The frame 922 and the expandable member 940 may be formed of dissimilar materials. The frame 922 may be formed of similar materials as the frame 920 described with respect to FIG. 9A.

To perform the procedure of influencing the size of the mitral annulus, for example for treating the patient's mitral regurgitation, the expandable member 940 and the larger, proximal end of frame 922 are compressed or crimped and loaded into the distal end of a delivery system (not shown). This action also causes the distal or narrower end of frame 930 to invert. Such inversion must be restrained for loading into the delivery system.

Once positioned in the desired location proximate the heart valve annulus, such as the mitral valve annulus, the frame 922 is advanced out from the distal end of the delivery system, inverting as it is no longer constrained by the delivery system and expandable member 940 remains in the crimped configuration. The distal ends or distal apices of frame 922 are then positioned in abutting relationship to the target cardiac tissue proximate the mitral valve annulus. Helical piercing members 930 are then rotationally advanced into and in engagement with the target heart tissue in a manner very similar to the helical screw of a corkscrew advancing through a cork. The expandable member 940 is then expelled from the delivery system and forcibly expanded, for example by dilatation balloon which balloon could be an integral component of the delivery system. Expansion of the stent-like expandable member 940 causes frame 922 to revert to its nominal or free state thereby causing its distal apices and helical anchors to become narrower in diameter reducing the size of the mitral annulus and limiting the degree or extent of mitral regurgitation.

FIGS. 10, 11 and 12 are various views of another embodiment of an implant 1010. In this embodiment, the implant 1010 has a frame 1020 and an expandable member 1040 that are not formed as an integral implant, as for example in FIGS. 9A and 9B. Rather expandable member 1040 is positioned within frame 1020 proximate the proximal end thereof. Frame 1020 is made from a nickel titanium alloy, such as Nitinol, whereas expandable member 1040 is preferably made of metallic alloys such as stainless steel, cobalt chromium, platinum iridium and the like.

FIG. 10 shows frame 1020 in its free or unconstrained state with expandable member 1040 crimped and positioned within frame 1020. One or more holes 1050 are pre-drilled in the distal ends or apices of frame 1020 and oriented to accommodate the pitch of helical anchors (not shown for clarity) such as the anchors 930 of FIGS. 9A and 9B. The anchors 930 may be rotated through the holes 1050 to advance the anchors 930 distally, i.e. downward as oriented in the figure. In some embodiments, the anchors 930 may be rotated in the opposite direction through the holes 1050 to retract the anchors 930 in the opposite, proximal direction. FIG. 11 shows the frame 1020 in a constrained configuration and implant 1010 ready for loading into the distal end of a delivery system (not shown). FIG. 12 shows implant 1010 in what would be its deployed configuration. While expandable member 1040 is shown to have a diamond like lattice configuration, it is contemplated that it may also take the form of a sinusoid or a hexagonal configuration.

Delivery of implant 1010 may be conducted in similar respect to the embodiment of FIG. 9A. More specifically, implant 1010 is loaded into the distal end of a delivery system (not shown), by compressing or collapsing frame 1020 as shown in FIG. 11 . Once positioned in a desired location proximate the mitral valve annulus, frame 1020 is advanced out of the delivery system and its distal apices are abutted to the target heart tissue for anchor placement. The helical anchors (not shown) are then advance, by rotation thereof, into the target cardiac tissue thereby anchoring implant 1010 into the region of the mitral valve annulus. Implant 1010 is then fully released from the delivery system.

After implant 1010 is fully released from the delivery system, expandable member 1040 is then forcibly expanded, such as by a dilatation balloon, causing frame 1020 to invert as shown in FIG. 12 . Inversion of frame 1020 causes the anchor bearing distal end of frame 1020 to taper or contract, causing the mitral valve annulus to reduce in size thus limiting the mitral valve regurgitation.

FIG. 13 shows an exemplary steerable delivery system 950, including for example a catheter or catheter lumen, suitable for delivery of the various implant embodiments described herein. FIG. 13 depicts an embodiment of the implant 1010 of FIGS. 10-12 , but it is understood that the delivery system 950 can be used to delivery other implants, including but limited to the implant 912 of FIG. 9B and the implant 910 of FIG. 9A, the latter of which is further shown in and described with respect to FIG. 14 . For example, a similar delivery system 950 may be used for the implant 912 embodied in FIG. 9B. For brevity and since the expandable members are different between the aforementioned embodiments, the expandable members 1040 are not shown in FIG. 13 .

The delivery system 950 may include a tube or tube-like structure having one or more lumens extending therethrough. For instance, the delivery system 950 may include an elongated tube or delivery catheter having one or more openings, i.e. lumens, extending therethrough and configured to receive therein, or having therein, corresponding features of the delivery system 950, including but not limited to the guide wire 160, the catheter 140, one or more of the drivers 952, and the intracardiac echo catheter 960. In some embodiments, the delivery system 950 includes a delivery catheter having a lumen to guide the delivery catheter over the guide wire, another lumen or lumens that include(s) the rotatable drivers 952, the implant 912 in a constrained delivery configuration located at a distal end of the delivery catheter, and a sheath covering the distal end of the catheter. Delivery system 950 is advanced transfemorally, either through the femoral vein and transeptally to the left atrium or through the femoral artery up through the aortic arch and then passed the aortic and mitral valves into the left atrium. Once positioned above mitral annulus and proximate the target heart tissue, the implant is partially released, releasing the frame portion 920, 1020. Frame 920, 1020 is now unconstrained and able to return to its nominal or free state as shown in FIG. 13 .

Helical piercing members 930 are then rotationally advanced into the target cardiac tissue, anchoring the implant to the interior heart wall above the mitral annulus. The implant and expandable member 940, 1040 is then released from delivery system 950. At such time, the stent like member 940, 1040 is forcibly expanded causing the frame 920, 1020 to invert. The distal end of apices and helical anchors 930 are then cinched inwardly reducing the diameter of the distal end of frame 920, 1020 causing a corresponding reduction in the size of the mitral annulus. This reduction in size of the mitral annulus, allows the mitral valve leaflets to better, if not completely, coapt reducing the severity of the patient's mitral regurgitation.

In a further embodiment of the present invention, an intracardiac echo catheter 960 is incorporated in delivery system 950. Catheter 960 could be included in a lumen of delivery system 950, either internally as shown, or alongside implant delivery system 950. By rotating catheter 960 within the left atrium and proximate the mitral valve annulus, the relative position of the implant with respect to the mitral valve leaflets can be determined. This allows for accurate positioning of helical anchors 930 into the target heart tissue proximate the mitral annulus without piercing the mitral valve leaflets.

FIG. 14 depicts the steerable delivery system 950 being used to deliver the implant 910 of FIG. 9A. The description of the delivery system 950 above with respect to FIG. 13 applies to use of the system 950 with the implant 910, and vice versa, except as otherwise noted. As shown in FIG. 14 , the implant 910 thus includes the frame 920 and expandable member 940, shown as integral with the frame 920. In some embodiments, the implant 910 may only include the frame 920. The delivery system 950 may or may not include the intracardiac echo catheter 960, as described above.

As shown in FIG. 14 , a plurality of rotational drivers 952 extends out through a distal opening of a lumen of the delivery catheter and/or sheath of the delivery system 950. Each driver 952 may extend through a corresponding lumen of the delivery system 950. In some embodiments, more than one or all of the drivers 952 may extend through the same lumen of the delivery system 950. A guide wire, such as the guide wire 160, may also be incorporated into the delivery system 950, and may extend through a lumen of the delivery system 950.

The drivers 952, only some of which are labelled for clarity, are each engaged with a corresponding rotational anchor 930. The drivers 952 may be pre-engaged with the anchors 930 within the delivery catheter of the delivery system 950 before insertion of the distal end of the delivery system 950 into the atrium. The drivers 962 may be mechanically engaged with the anchors 930 in a variety of suitable approaches. For example, the drivers 962 may have a clevis type fitting as shown configured to surround the proximal end of the anchors 930. The drivers 952 may extend over, on, under, etc. the proximal ends of the anchors 930 and then be rotated to transmit rotation to the anchors 930. In some embodiments, the anchors 930 may have recesses or other tool-receiving portions engaged by the drivers 952 such that rotation of the drivers 952 is transmitted to the anchors 930. In some embodiments, the drivers 952 may include socket type fittings that surround the anchors 930. In some embodiments, the anchors 930 may have internally-threaded blind holes through which corresponding externally-threaded members of the drivers 952 are received. These are merely some examples of how the drivers 952 may be engaged with the anchors 930, and other suitable approaches may be implemented. With the implant 910 in position for anchoring to the annulus, a proximal end of the drivers 962 may be manipulated by the user, for example rotated by the surgeon, to rotate the anchors 930 and thereby advance the anchors 930 into heart tissue, as described herein, to secure the implant 910 with the heart tissue. Each driver 952 may be actuated simultaneously, some may be actuated simultaneously, or they may be actuated sequentially. The anchors 930 may extend distally relative to the frame, as described herein.

FIGS. 15A-15D show sequential views of an embodiment of a transcatheter delivery system for delivering the implant 910 showing an embodiment of a method for the delivery, positioning and anchoring of the implant 910 for resizing the native valve annulus. The various delivery systems as described herein may be used. As shown, the delivery system may include the sheath 150, the catheter 140 and the guide wire 160. The sheath 150, the catheter 140, the guide wire 160 and the implant 910 are configured for transcatheter delivery of the implant 910 to the heart. The implant 910 may be delivered by the delivery system percutaneously by catheter through an opening in the femoral vein. The implant 910 may be advanced through the femoral vein into the vena cava and into the right atrium. The distal ends of the sheath 150, catheter 140, and guide wire 160 are configured to extend through the opening in the femoral vein, through the femoral vein and into the right atrium of the heart, and through the septum of the heart into the left atrium.

As shown in FIG. 15A, the guidewire 160 may be advanced through the septum separating the upper chambers of the heart and the sheath 150 and catheter 140 may be advanced to that position along the guide wire 140. The distal end of the catheter 140 is advanced to a position above the heart valve annulus, for example, the mitral valve annulus, as shown in FIG. 15B. FIG. 15C shows the implant 910 expelled from the distal end of the sheath 150 above and proximate to the mitral valve annulus. In some embodiments, a series of images may be taken, for example with an intracardiac echo catheter, to properly position the anchors 930 for insertion into the mitral valve annulus tissue. As shown in FIGS. 15C and 15D, the anchors 930 may be rotationally engaged by rotational drivers of the delivery system, such as the drivers 952 described herein, for rotation and distal advancement of the anchors 930 into the heart valve annulus. In some embodiments, a circumferential image may be captured to confirm that all anchors 930 are appropriately placed and anchored in the mitral valve annulus tissue above the mitral valve leaflets. If one or more anchors 930 are not positioned or anchored properly, the drivers 952 may reverse the direction of rotation to rotationally retract the anchors in the proximal direction. The anchors 930 can then be repositioned and re-anchored prior to removal of the drivers 952.

Though a particular path of transcatheter delivery is described with respect to FIGS. 15A-15D, a variety of other delivery paths and approaches may be employed, including but not limited to the paths shown and described with respect to FIGS. 1A-1F, trans-apical delivery, etc. In addition, any of the features and/or functionalities of the delivery system and associated methods described with respect to FIGS. 1A-1F may be incorporated with respect to the delivery system and methods described with respect to FIGS. 15A-15D, and vice versa. Therefore, for example, with regard to the delivery system and methods described with respect to FIGS. 15A-15D, the implant 910 may “invert” as described herein, an expandable or fixed ring 320 may be utilized as described, the location ring 120 may be inserted below the valve, etc.

This disclosure encompasses all changes, substitutions, variations, alterations, and modifications to the example embodiments herein that a person having ordinary skill in the art would comprehend. Similarly, where appropriate, the appended claims encompass all changes, substitutions, variations, alterations, and modifications to the example embodiments herein that a person having ordinary skill in the art would comprehend. Moreover, reference in the appended claims to an apparatus or system or a component of an apparatus or system being adapted to, arranged to, capable of, configured to, enabled to, operable to, or operative to perform a particular function encompasses that apparatus, system, component, whether or not it or that particular function is activated, turned on, or unlocked, as long as that apparatus, system, or component is so adapted, arranged, capable, configured, enabled, operable, or operative. For example, various embodiments may perform all, some, or none of the steps described above. Various embodiments may also perform the functions described in various orders.

Although the present disclosure has been described above in connection with several embodiments; changes, substitutions, variations, alterations, transformations, and modifications may be suggested to one skilled in the art, and it is intended that the present disclosure encompass such changes, substitutions, variations, alterations, transformations, and modifications as fall within the spirit and scope of the appended claims. 

1. (canceled)
 2. A device for adjusting cardiac tissue, said device comprising: a frame; and a tissue-engaging element; wherein: said frame is expandable from a collapsed configuration to an expanded configuration for deployment of said frame with respect to the cardiac tissue; said frame is movable with respect to the cardiac tissue to contract the annular cardiac tissue; and said frame and said tissue-engaging element are rotatable with respect to each other.
 3. The device of claim 2, wherein a component of said device is rotatable with respect to the cardiac tissue
 4. The device of claim 2, wherein a component of said device is rotatable to engage with the cardiac tissue.
 5. The device of claim 2, wherein a component of said device is rotatable when engaged with the cardiac tissue.
 6. The device of claim 2, wherein said frame is expandable by expansion of a balloon element with respect thereto.
 7. The device of claim 2, wherein said frame is formed from a plurality of struts.
 8. The device of claim 2, wherein said tissue-engaging element includes an at least partially annular configuration.
 9. The device of claim 2, wherein said tissue-engaging element is axially movable with respect to said frame.
 10. A device for adjusting cardiac tissue, said device comprising: a frame; and a securing element; wherein: said frame is expandable from a collapsed configuration to an expanded configuration for deployment of said frame with respect to the cardiac tissue; said frame is movable with respect to the cardiac tissue to contract the cardiac tissue; and said securing element is axially movable with respect to said frame and the cardiac tissue to secure a contracted configuration of the cardiac tissue.
 11. The device of claim 10, wherein said frame and said securing element are rotatable with respect to each other.
 12. The device of claim 10, wherein said frame is expandable by expansion of a balloon element with respect thereto.
 13. The device of claim 10, wherein said frame is formed from a plurality of struts.
 14. The device of claim 10, wherein said securing element engages cardiac tissue.
 15. The device of claim 10, wherein said securing element includes an at least partially annular configuration.
 16. A system for adjusting annular cardiac tissue, said system comprising: an implantable device; and a delivery system rotatable to adjust said implantable device with respect to cardiac tissue to adjust the configuration of the cardiac tissue.
 17. The system of claim 16, further comprising rotatable drivers operatively coupled with said implantable device.
 18. The system of claim 16, further comprising a catheter rotatable to adjust said implantable device with respect to cardiac tissue.
 19. The system of claim 16, further comprising a locking mechanism configured to retain the adjusted configuration of the cardiac tissue.
 20. The system of claim 19, wherein said locking mechanism is ring-shaped.
 21. The system of claim 20, wherein said locking mechanism is axially movable with respect to said implantable device. 